Medical optical imaging scanner using multiple wavelength simultaneous data acquisition for breast imaging

ABSTRACT

A scanner for a medical optical imaging device, comprises an illumination source positioned to direct emitted light into a breast positioned below a support surface; first and second groups of photodetectors positioned in an arc around the breast to simultaneously detect light emerging from the breast; and optical filters disposed in front of the first group of photodetectors to restrict the wavelength of light reaching the first group of photodetectors.

RELATED APPLICATION

[0001] This is a nonprovisional application claiming the prioritybenefit of provisional application serial No. 60/202,933, filed May 9,2000, which is hereby incorporated by reference.

FIELD OF THE INVENTION

[0002] The present invention generally relates to diagnostic medicalimaging apparatus and more particularly to a mammography machine thatemploys a near-infrared laser as a radiation source.

BACKGROUND OF THE INVENTION

[0003] Cancer of the breast is a major cause of death among the Americanfemale population. Effective treatment of this disease is most readilyaccomplished following early detection of malignant tumors. Majorefforts are presently underway to provide mass screening of thepopulation for symptoms of breast tumors. Such screening efforts willrequire sophisticated, automated equipment to reliably accomplish thedetection process.

[0004] The x-ray absorption density resolution of present photographicx-ray methods is insufficient to provide reliable early detection ofmalignant tumors. Research has indicated that the probability ofmetastasis increases sharply for breast tumors over 1 cm size. Tumors ofthis size rarely produce sufficient contrast in a mammogram to bedetectable. To produce detectable contrast in photographic mammograms,2-3 cm dimensions are required. Calcium deposits used for inferentialdetection of tumors in conventional mammography also appear to beassociated with tumors of large size. For these reasons, photographicmammography has been relatively ineffective in the detection of thiscondition.

[0005] Most mammographic apparatus in use today in clinics and hospitalsrequire breast compression techniques which are uncomfortable at bestand in many cases painful to the patient. In addition, x-rays constituteionizing radiation which injects a further risk factor into the use ofmammographic techniques as most universally employed.

[0006] Ultrasound has also been suggested, as in U.S. Pat. No.4,075,883, which requires that the breast be immersed in a fluid-filledscanning chamber. U.S. Pat. No. 3,973,126 also requires that the breastbe immersed in a fluid-filled chamber for an x-ray scanning technique.

[0007] In recent times, the use of light and more specifically laserlight to noninvasively peer inside the body to reveal the interiorstructure has been investigated. This technique is called opticalimaging. Optical imaging and spectroscopy are key components of opticaltomography. Rapid progress over the past decade have brought opticaltomography to the brink of clinical usefulness. Optical wavelengthphotons do not penetrate in vivo tissue in a straight line as do x-rayphotons. This phenomenon causes the light photons to scatter inside thetissue before the photons emerge out of the scanned sample.

[0008] Because x-ray photon propagation is essentially straight-line,relatively straight forward techniques based on the Radon transform havebeen devised to produce computed tomography images through use ofcomputer algorithms. Multiple measurements are made through 360° aroundthe scanned object. These measurements, known as projections, are usedto back project the data to create an image representative of theinterior of the scanned object.

[0009] In optical tomography, mathematical formulas and projectiontechniques have been devised to perform a reconstruction functionsomewhat similar to x-ray tomography. However, because light photonpropagation is not straight-line, techniques to produce cross-sectionimages are mathematically intensive and invariably require establishingthe boundary of the scanned object. Boundary determination is importantbecause it serves as the basis for reconstruction techniques to produceinterior structure details. Algorithms to sate do not use any form ofdirect measurement techniques to establish the boundary of the scannedobject.

[0010] Addition information concerning the interior of the breast can beobtained when a scanner is able to acquire data resulting fromilluminating the breast with different wavelengths or from acquiringinformation pertaining to light emitted by fluorescent materialsintroduced into the breast.

OBJECTS AND SUMMARY OF THE INVENTION

[0011] It is an object of the present invention to provide a scanner fora medical optical imaging device that uses a fluorescent marker toprovide an enhanced identification of an abnormality within the breastbeyond the inherent localized changes in optical scattering andabsorption.

[0012] It is another object of the present invention to provide ascanner for a medical optical imaging device that provides forsimultaneous acquisition of optical data at multiple wavelengths.

[0013] It is still another object of the present invention to provide ascanner for a medical optical imaging device that provides forsimultaneous acquisition of data from at least two planes within thebreast.

[0014] It is another object of the present invention to provide ascanner for a medical optical imaging device that provides forsimultaneous acquisition of attenuation data and fluorescence data.

[0015] It is another object of the present invention to provide ascanner for a medical optical imaging device that provides for acquiringpre- and post-injection of a contrast agent, such as Indocynine Green(ICG) of both attenuation and fluorescence data and reconstructing theimage from the difference between the raw data sets.

[0016] In summary, the present invention provides a scanner for amedical optical imaging device, comprising an illumination sourcepositioned to direct emitted light into a breast positioned below asupport surface; first and second groups of photodetectors positioned inan arc around the breast to simultaneously detect light emerging fromthe breast; and optical filters disposed in front of the first group ofphotodetectors to restrict the wavelength of light reaching the firstgroup of photodetectors.

[0017] The present invention also provides an apparatus for imaging abreast, comprising a scanning chamber for receiving therein the breastto be scanned; a laser beam disposed within the scanning chamber forimpinging on the breast, the laser beam being adapted to orbit aroundthe breast; first and second groups of detectors positioned in an arcaround the breast to simultaneously detect light emerging from thebreast to generate first and second projection data, respectively;optical filters operably associated with the first group of detectors torestrict the wavelength of light reaching the first group of detectorsto the wavelength of radiation emitted by a contrast agent introducedinto the breast after being activated by the beam; and a computer toreconstruct an image of the breast from projection data derived fromsubtracting first and second baseline projection data prior tointroduction of the contrast agent into the breast from respective firstand second projection data obtained after introduction of the contrastagent.

[0018] The present invention further provides a method for collectingdata for use in image reconstruction of a breast being scanned,comprising providing a beam of laser; providing a contrast agent withinthe breast; orbiting the laser beam around the breast clockwise toobtain a first set of projection data; orbiting the laser beam aroundthe breast counterclockwise to obtain a second set of projection data;providing first and second groups of detectors positioned in an arcaround the breast to detect light emerging from the breast to generatethe first and second sets of projection data, respectively; restrictingthe first group of detectors to the wavelength of radiation emitted by acontrast agent within the tissue after being activated by said laserbeam; and subtracting first and second baseline projection data obtainedprior to introduction of the contrast agent into the breast fromrespective first and second projection data obtained after the contrastagent has been introduced to obtain respective differential projectiondata to be used in image reconstruction.

[0019] These and other objects of the present invention will becomeapparent from the following detailed description.

BRIEF DESCRIPTIONS OF THE DRAWINGS

[0020]FIG. 1 is a schematic side elevational view of a medical opticalimaging device showing a patient positioned on a support with her breastpendent within a scanning chamber made in accordance with the presentinvention,.

[0021]FIG. 2 is an enlarged schematic side elevational view of thescanner shown in FIG. 1.

[0022]FIG. 3 is a schematic diagram of a signal processing system usedin the present invention.

[0023]FIG. 4 is a perspective view of a collimator made in accordancewith the present invention, showing a plurality of openings to restrictthe field of view of detectors.

[0024]FIG. 5 is an enlarged fragmentary perspective view of a portion ofthe collimator shown in FIG. 4, showing the incorporation of filter forthe upper row of detectors.

[0025]FIG. 6 is schematic plan view of the scanner, showing therelationship between the patient's breast, illumination beam,collimator, detector field of view, and the detector. FIG. 6 is a graphshowing the spectral response for the detector, laser beam, fluorescenceemission wavelengths and the optical filter spectral response.

[0026]FIGS. 8A and 8B are flow diagrams showing data acquisition formask data and projection data.

[0027]FIG. 9 is a flow diagram showing the subtraction of mask data fromrespective slice date projection prior to image reconstruction.

DETAILED DESCRIPTION OF THE INVENTION

[0028] A medical optical imaging device is disclosed in U.S. Pat. Nos.5,692,511, 6,100,520, and 6,130,958, which are hereby incorporated byreference.

[0029] Referring to FIGS. 1 and 2, a patient 2 is positioned prone on ascanning table 4 with one breast 6 pendulant in a scanning chamber 8through an opening 3 through the table. A medical optical imagingscanner 10 comprises a laser beam 11 and a collimator 12 secured to anorbit plate 14 and an elevator plate 16. The collimator 12 is associatedwith photodetectors 22 (see FIG. 4), such as photodiodes. The orbitplate 14 is orbited through one circle around the breast to obtain a setof data. The elevator plate 16 is moved vertically by drive screws 18 toposition the orbit plate 14 at different vertical locations where theorbit plate 14 is again orbited through one circle around the breast toobtain another set of data.

[0030] Referring to FIG. 3, a schematic diagram of an electronic dataacquisition system 20 is disclosed. It should be understood that anumber of photodetectors 22 are used, configured in an arc around thebreast, although only one photodetector 22 is shown for clarity. Lightimpinging on photodetector 22, such as a photodiode, causes a current toflow. Each photodetector 22 is connected to its own integrator 24 whichproduces a voltage output proportional to the amount of currentgenerated by the photodetector 22. The voltage output is coupled to anelectronic multiplexer 26. The output of the multiplexer 26 is coupledto an analog-to-digital converter (ADC) 28 to provide a digitizedoutput, which is coupled to a computer 30 where the digitized output isstored for future use. Examples of the system 20 are disclosed in U.S.Pat. No. 6,150,649 and co-pending application Ser. No. 09/199,440, filedNov. 25, 1998, both of which are hereby incorporated by reference.

[0031] Referring to FIG. 4, the collimator 12 comprises a series ofholes 32 through a body 34 that arches around the breast 6.Photodetectors 22 are positioned at the end of each hole 32 to detectlight coming from the breast 6 due to the laser beam 11 impinging on thebreast during scanning. A lens 38 may be placed in front of eachphotodetector 22 to increase light collection capability.

[0032] The collimator holes 32 are arranged into an upper row and alower row. The horizontal centerline through each hole 32 along theupper row of holes 32 is parallel to the centerline of each hole 32along the lower row. The centerlines for the upper row of holes define aplane 41 through the breast. The centerlines for the holes in the lowerrow define another plane 43. The upper row of holes The vertical centerline of each hole in the upper row may be in line with the verticalcenter line of a corresponding hole in the lower row. Alternately, thevertical center line of each hole in the upper row may be interdigitatedor horizontally offset with the vertical center line of the holes in thesecond row to minimize the vertical separation between the two rows.

[0033] Referring to FIG. 5, an optical cut-off or band pass filter 40 isplaced in front of each photodetector 22 associated with the upper rowof holes 32 to limit the photodetector's spectral response to thedesired range of wavelength. A holding block 42 is used to hold theassembly together and accurately position the photodetectors 22. Machinescrews 44 hold the block 42 to the body 34. It should be understood thata number of the holding blocks 42, along with their respectivephotodetectors, would be used, although only one is shown for clarity.The holding block 42 has openings 46 to allow the light passing throughthe holes 32 to reach the respective photodetectors 22.

[0034] The collimator 12 is shown schematically in plan view in FIG. 6.Each opening 32 is directed to the center of rotation 45 of the scanner.Each opening 32 has a field of view, schematically indicated at 39, torestrict the amount and direction of light that can be detected by thephotodetectors 22. Examples of collimators are disclosed in U.S. Pat.No. 6,100,520, which is hereby incorporated by reference.

[0035] The scanner 10 is used to simultaneously acquire data at twodifferent wavelengths. One set of data corresponding to one wavelengthis acquired by the photodetectors associated with the upper row of holes32 and another set of data corresponding to another wavelength isacquired by the photodetectors associated with the lower row of holes32. This is accomplished by limiting the exposure of the upper or lowerrow of photodetectors to certain wavelengths by means of the filter 40.The filter 40 blocks all of the light transmitted through the breast atthe laser source wavelength while permitting fluorescent light to bedetected. The other row of photodetectors detect the sum of the lighttransmitted through the breast and the fluorescent light emitted fromwithin the breast. With this configuration, both the effectiveattenuation and fluorescent images maybe reconstructed from a singlerotation of the scanner around the breast.

[0036] Referring to FIG. 7, the spectral response for the photodetector22 is indicated at 48. The laser beam wavelength is generally indicatedat 50. A fluorescence absorption wavelength band is generally indicatedat 52. The fluorescence emission wavelength band is generally indicatedat 54. The filter 40 is an optical cut-off filter that prevents light atthe absorbance wavelength 52 from reaching the photodetectors, butpermits any light due to fluorescence emission 54. The filter limits theexposure of the filtered photodetectors to those wavelengths longer thanthe filter cut-off wavelength, generally indicated at 56. The filter 40may also be a bandpass filter.

[0037] Data from the filtered set of photodetectors are used toreconstruct a fluorescent image of areas within the breast. Fluorescenceis introduced into the breast through use of a fluorophore, such asIndocynine Green or an appropriate contrast agent that is injected intothe bloodstream or otherwise introduced into the breast. The fluorophoreis excited by the laser source, causing it to emit fluorescent light.Data from the unfiltered row of photodetectors are used to reconstructan absorption image of the breast. Since the perimeter of the breast isacquired during scanning of the breast, the absorption and fluorescentimages, which are reconstructed using the unfiltered laser light and thefluorescent emission caused by the excitation of the fluorophore by thescanning laser beam, are automatically co-registered within theperimeter. Examples of means for acquiring the perimeter of the breastduring scanning are disclosed in U.S. Pat. Nos. 6,044,288 and 6,029,077,incorporated herein by reference.

[0038] Use of a fluorophore is further disclosed in U.S. Pat. No.5,952,664, issued on Sep. 14, 1999, which is hereby incorporated byreference.

[0039] The digitized signals stored in the computer 30 is hereinreferred to as projection data, which are used to reconstruct an imageof the breast, as disclosed in U.S. Pat. No. 6,130,958, herebyincorporated by reference. Referring to FIGS. 8A and 8B, a flow diagramfor a series of projection data acquisitions is disclosed. The patientis positioned prone on the scanning table 4 with her breast 6 placedthrough the opening in the scanning chamber 18. The laser beam andphotodetectors 22 are rotated together 360° in one direction around thebreast and one set of projection data is acquired, corresponding to theupper and lower rows of detectors. At the completion of the acquisition,the direction of rotation of the scanner is reversed and another set ofprojection data are acquired corresponding to the upper and lower rowsof detectors. This series of data acquisition is generally indicated at60.

[0040] References to “mask” and “slice” in FIGS. 8A, 8B and 9 and belowrefer to the two sets of data simultaneously acquired by the upper andlower rows of photodetectors as the scanner is rotated in a clockwise orcounterclockwise direction, where one set of data corresponds to theupper row of photodetectors scanning the breast through the plane 41,and the other set of data corresponds to the lower row of photodetectorsscanning through the plane 43 (see FIG. 2).

[0041] To establish a pre-injection baseline, the first and second setsof projection data, referred to as clockwise (CW) mask 62 andcounterclockwise (CCW) mask 64, respectively, are taken prior to the ICGinjection, as indicated at 65. After the CW mask 62 and the CCW mask 64are acquired, the scan continues at the same vertical position of thescanner with repeated acquisitions of projection data, with dataacquired with a clockwise rotation being referred to as slice CW data 66and the counterclockwise data as slice CCW data 68.

[0042] After the CW mask 62 and CCW mask 64 are taken, a contrast agent,such as Indocynine Green (ICG), is injected into the body, as generallyindicated at 70. ICG is a standard diagnostic aid for blood flowmeasurements. Data acquisitions continue for a period of time,alternating between CW data 66 and CCW data 68 until the ICG clears thesystem, generally indicated at 72.

[0043] Referring to FIG. 9, after the data acquisition sequence iscompleted, data subtractions at 74 and 76 are performed prior to imagereconstruction. Since optical image reconstruction algorithms areiterative that exhibit non-linear characteristics because of negativityand relaxation constraints, projection data are subtracted rather thanthe reconstructed images. For data acquired with clockwise rotation,slice data 66 and mask data 62 are used. Digital subtraction isperformed with the mask data 62 being subtracted from the respectiveslice data 66 to derive image projection data to reconstruct images 78.Similarly, digital subtraction at 76 is performed with mask data 64being subtracted from the respective slice data 68 to derive imageprojection data to reconstruct images 80. In the subtraction, it shouldbe understood that the upper or lower row component of the mask data issubtracted from the respective upper or lower row component of the slicedata. This subtraction process results in an image that contains onlythe information that is new in the images obtained after use of thecontrast agent. A time-series of images of the breast are therebycreated, showing fluorescent images as the ICG arrives and perfuses thebreast, which may be used to demonstrate uptake, washout, etc. of thecontrast agent.

[0044] In the data acquisition sequence described above, the scanner isstationary at a certain vertical position where the lesion in the breastis expected to exhibit the largest cross-sectional area through theslice plane.

[0045] Where the scanner 10 is used for a single wavelength, the filters40 would be removed and the mask data would not be obtained, sincesubtraction would not be performed.

[0046] In addition to photodiodes, the photodetectors 22 may also beavalanche photodiodes, photo-multiplier tubes, micro-channel plates,charged coupled devices (CCD) or other photodetectors.

[0047] While this invention has been described as having preferreddesign, it is understood that it is capable of further modification,uses and/or adaptations following in general the principle of theinvention and including such departures from the present disclosure ascome within known or customary practice in the art to which theinvention pertains, and as may be applied to the essential features setforth, and fall within the scope of the invention or the limits of theappended claims.

We claim:
 1. A scanner for a medical optical imaging device, comprising:a) an illumination source positioned to direct emitted light into abreast positioned below a support surface; b) first and second groups ofphotodetectors positioned in an arc around the breast to simultaneouslydetect light emerging from the breast; and c) optical filters disposedin front of said first group of photodetectors to restrict thewavelength of light reaching said first group of photodetectors.
 2. Ascanner as in claim 1, wherein said filters are cut-off filters.
 3. Ascanner as in claim 1, wherein said filters are band pass filters.
 4. Ascanner as in claim 1, wherein said first and second groups ofphotodetectors are arranged in respective first and second rows.
 5. Ascanner as in claim 4, wherein said first row is disposed above saidsecond row.
 6. A scanner as in claim 4, wherein said first row isparallel to said second row.
 7. A scanner as in claim 4, wherein saidfirst row is horizontally offset from said second row.
 8. A detectorarray, comprising: a) first and second groups of detectors positioned inan arc around the breast to simultaneously detect light emerging fromthe breast; and b) optical filters operably associated with said firstgroup of detectors to restrict the wavelength of light reaching saidfirst group of detectors to the wavelength of radiation emitted by acontrast agent within the tissue after being activated by a laser beam.9. A detector array as in claim 8, wherein said filters are cut-offfilters.
 10. A detector array as in claim 8, wherein said filters areband pass filters.
 11. A detector array as in claim 8, wherein saidfirst and second groups of detectors are arranged in respective firstand second rows.
 12. A detector array as in claim 11, wherein: a) saidfirst row is disposed above said second row; and b) said first row isparallel to said second row.
 13. A detector array as in claim 11,wherein said first row is horizontally offset from said second row. 14.An apparatus for imaging a breast, comprising: a) a scanning chamber forreceiving therein the breast to be scanned; b) a laser beam disposedwithin said scanning chamber for impinging on the breast, said laserbeam being adapted to orbit around the breast; c) first and secondgroups of detectors positioned in an arc around the breast tosimultaneously detect light emerging from the breast to generate firstand second projection data, respectively; d) optical filters operablyassociated with said first group of detectors to restrict the wavelengthof light reaching said first group of detectors to the wavelength ofradiation emitted by a contrast agent introduced into the breast afterbeing activated by said beam; and e) a computer to reconstruct an imageof the breast from projection data derived from subtracting first andsecond baseline projection data prior to introduction of the contrastagent into the breast from respective first and second projection dataobtained after introduction of the contrast agent.
 15. An apparatus asin claim 14, wherein said first baseline projection data is obtainedfrom said first and second groups of detectors during a clockwiserotation thereof.
 16. An apparatus as in claim 14, wherein said secondbaseline projection data is obtained from said first and second groupsof detectors during a counterclockwise rotation thereof.
 17. Anapparatus as in claim 14, wherein said filters are cut-off filters. 18.A detector array as in claim 14, wherein said filters are band passfilters.
 19. A detector array as in claim 14, wherein said first andsecond groups of detectors are arranged in respective first and secondrows.
 20. A detector array as in claim 14, wherein: a) said first row isdisposed above said second row; and b) said first row is parallel tosaid second row.
 21. A method for collecting data for use in imagereconstruction of a breast being scanned, comprising: a) providing abeam of laser; b) providing a contrast agent within the breast; c)orbiting the laser beam around the breast clockwise to obtain a firstset of projection data; d) orbiting the laser beam around the breastcounterclockwise to obtain a second set of projection data; e) providingfirst and second groups of detectors positioned in an arc around thebreast to detect light emerging from the breast to generate the firstand second sets of projection data, respectively; f) restricting thefirst group of detectors to the wavelength of radiation emitted by acontrast agent within the tissue after being activated by said laserbeam; and g) subtracting first and second baseline projection dataobtained prior to introduction of the contrast agent into the breastfrom respective first and second projection data obtained after thecontrast agent has been introduced to obtain respective differentialprojection data to be used in image reconstruction.
 22. A method as inclaim 21, wherein the contrast agent is a fluorophore.
 23. A method asin claim 21, wherein the contrast agent is Indocynine Green.
 24. Amethod as in claim 21, wherein said limiting is implemented with acut-off filter.